Breath-controlled inhalation therapy device

ABSTRACT

A breath-controlled inhalation therapy device includes an obturation mechanism, obturating a nozzle opening through which a pressurised gas, preferably pressurised air, is issued when the device is in operation. An actuation mechanism actuates the obturation mechanism only in the exhalation phases of the respiration cycle of a patient. The fluid to be atomised is therefore substantially atomised only in the inhalation phases.

CROSS REFERENCE TO RELATED APPLICATION

This application is a continuation of U.S. patent application Ser. No.11/921,206 filed Mar. 17, 2009, which is hereby incorporated byreference in its entirety.

DESCRIPTION

The invention relates to a breath-controlled inhalation therapy devicefor the provision of an aerosol for use by a patient as part of aninhalation therapy.

A device of the type described above is known, for example, from US2004/0173209 A. In this device, an aerosol is generated using a nozzle,in that a compressed gas, for example compressed air, flowing out of anozzle opening draws a liquid to be nebulised through inlet channels andnebulises it upon exit out of outlet openings adjacent to the nozzleopening. A baffle is disposed in front of the nozzle, which, during anebulising operation, is disposed close to the nozzle openings in theinhalation phases and ensures that the exiting compressed gas isdiverted, which causes the drawing and nebulising action on the liquidto be nebulised. The baffle is shiftable and is moved away from thenozzle openings during the exhalation phases such that nebulisation nolonger takes place, even if the compressed gas continues to flow out ofthe nozzle opening. Breath control is thereby achieved in the knowndevice since it is only in the inhalation phases that the baffle ispositioned close enough to the nozzle openings to cause nebulisation.

Breath control is generally used in inhalation therapy nebulisers so asto prevent the loss of medicament or aerosol during exhalation phases.

The aim of the invention is to further improve the breath-controlledinhalation therapy devices.

This aim is achieved by means of a breath-controlled inhalation therapydevice for the provision of an aerosol for use by a patient as part ofan inhalation therapy, said device comprising a housing that defines anebulisation area, a nozzle opening for the entry of a pressurised gas,preferably compressed air, into the nebulisation area, at least oneoutlet opening for the entry of a liquid to be nebulised, preferably atherapeutically effective liquid, into the nebulisation area, a closingmeans for closing the nozzle opening, which is arranged in thenebulisation area relative to the nozzle opening in such a manner thatthe closing means can be moved into a position closing the nozzleopening and into a position unblocking the nozzle opening, and anactuation device for actuating the closing means in response to therespiratory cycle of the patient so as to actuate the closing meansduring the exhalation phase of a respiratory cycle of the patient suchthat the closing means assumes the position closing the nozzle opening.

The invention thereby makes use of the advantageous circumstance thatowing to the closing of the nozzle opening for the compressed gas,nebulisation is on the one hand reliably stopped and on the other hand,owing to the resistance generated for the compressed gas source, thereis normally an increase in pressure and buffering of compressed gas,which is temporarily available for nebulisation following reopening ofthe nozzle opening. This circumstance can be used, on the one hand, inlarger therapy devices to improve efficiency, even though these devicescan already be designed in a very efficient manner owing to their size.On the other hand, smaller therapy devices can be realised, which reachthe efficiency of the larger devices at a smaller size.

In a simple yet advantageous embodiment, the closing means is disposedopposite the nozzle opening. The required movement can thereby beeffected in a simple manner.

In the position exposing the nozzle opening, the closing meansadvantageously forms a baffle for the compressed gas exiting from thenozzle opening and the liquid exiting from the outlet opening. Theclosing means is therefore accorded a dual function which can berealised without any problems in one and the same component of thedevice according to the invention. No additional baffles or gas flowcontrol is therefore required according to the invention. However, theseelements can be additionally provided.

In an alternative design, the closing means is disposed to the side ofthe nozzle opening.

The device according the invention can thereby be designed in such amanner that the closing means for closing the nozzle opening acts on anozzle body consisting of a soft, flexible material, in which the nozzleopening is formed.

In order to achieve the best results as regards the sealing of thenozzle opening for the compressed gas, which is important for theinvention, the closing means is advantageously made, at least partly,out of a soft and flexible material. Alternatively or additionally, asealing portion made of a soft and flexible material can be provided atthe nozzle opening.

In order to ensure movement of the closing means, the actuation deviceadvantageously comprises a connecting means that connects the actuationdevice to the closing means. In this manner, arrangement of theactuation device in the inhalation therapy device according to theinvention can take place with more freedom. If the actuation device andthe closing means are disposed close to one another, the connectingmember of the actuation device can also be realised such that it is verysmall or can be dispensed with completely.

Particularly suitable for breath control is an actuation devicecomprising a piston member, with the pressure prevailing in the housingdetermining the position of the piston member.

In order to bring the piston into a defined position, the actuationdevice advantageously comprises a spring member that determines the restposition of the piston member.

In an advantageous embodiment, the actuation device comprises acylindrical member in which the piston can move. The spring member isthereby disposed in the compression space that is enclosed by the pistonmember and the cylindrical member. It is furthermore advantageous forthe cylindrical member to be formed by the housing.

Since the closing means has to be moved, the connecting means isconnected to the piston member since the piston member constitutes theelement of the actuation device that moves depending on breath.

Since an indication of the position of the closing means is desirable,the connecting means is advantageously extended beyond the piston membersuch that the connecting member protrudes out of the housing. Theposition of the protruding part is thus an indicator for the position ofthe closing means.

In order to prevent a counter-pressure in the compression space betweenthe piston and the cylinder of the actuation device, which could hindermovement, a ventilation passage is preferably provided for the inlet ofair to and outlet of air from the space enclosed by the piston memberand the cylindrical member during movement of the piston member in thecylindrical member.

In order to mechanically ensure and stabilise the movement of the pistonand the transmission of movement to the closing means, the actuationdevice preferably comprises a guide member in which the connectingmember is disposed.

In an embodiment that is favourable in terms of manufacturingtechnology, the connecting member is formed integrally with the closingmeans.

In inhalation therapy devices having a supply air duct, the actuationdevice is preferably disposed therein. The available space is thereforeoptimally used and the actuation device is accommodated such that it isprotected.

The invention will be described in more detail in the following by meansof embodiments and with reference to the drawings in which:

FIG. 1 shows a schematic sectional view of an embodiment of aninhalation therapy device according to the invention;

FIG. 2 shows a further schematic sectional view of the embodiment ofFIG. 1;

FIG. 3 shows a detailed representation of an advantageous design of theclosing means of an inhalation therapy device according to theinvention;

FIG. 4 shows a detailed representation of an advantageous design of thenozzle opening of an inhalation therapy device according to theinvention;

FIG. 5 shows a schematic sectional view of a further embodiment of aninhalation therapy device according to the invention;

FIG. 6 shows a further schematic sectional view of the embodiment ofFIG. 5;

FIG. 7 shows a schematic sectional view of a further embodiment of aninhalation therapy device according to the invention;

FIG. 8 shows a further schematic sectional view of the embodiment ofFIG. 8;

FIGS. 9A and 9B show a partial area of a further embodiment of aninhalation therapy device according to the invention; and

FIGS. 10A and 10B show a further embodiment of an inhalation therapydevice according to the invention.

FIG. 1 shows an inhalation therapy device 1 according to the inventionfor the provision of an aerosol for use by a patient as part of aninhalation therapy. In the embodiment shown in FIG. 1, the inhalationtherapy device 1 comprises a housing 2 that defines a nebulisation area3 in the interior thereof. During operation, an aerosol is generated inthe inhalation area 3 and is provided to a patient for inhalation. Thepatient inhales the aerosol via a mouthpiece 4 that is provided on theinhalation therapy device 1 and is connected to the interior 3 of thehousing 2. Furthermore, in the embodiment shown in FIG. 1, at least onenozzle opening 5 is provided in the nebulisation area 3, out of which apressurised gas, preferably compressed air, exits during operation andenters the nebulisation area 3. The compressed gas or compressed air issupplied via a supply line 6 to the device 1 from a compressed airsource, preferably a compressor, which is not shown in FIG. 1.

In the embodiment shown in FIG. 1, at least one outlet opening 7 isarranged adjacent to the nozzle opening 5 for the compressed gas, out ofwhich a liquid to be nebulised, preferably a therapeutically effectiveliquid, exits during operation and enters the nebulisation area 3. Theliquid 8 to be nebulised is stored in a liquid reservoir 9 of the device1, said reservoir 9 preferably forming part of the housing 2, asillustrated in the embodiment shown in FIG. 1. Since the liquid outletopening 7 is arranged adjacent to the nozzle opening 5, the compressedgas exiting out of the nozzle opening causes nebulisation of the liquidexiting out of the outlet opening. An effect is thereby preferably used,by means of which the liquid 8 to be nebulised is drawn through theinlet opening 7 owing alone to the fact that the compressed gas flowsout of the nozzle opening 5 and generates a negative pressure at theoutlet opening 7 for the liquid. Owing to the spatial proximity of thecompressed gas nozzle opening 5 and the liquid outlet opening 7 that isrequired herefor, the compressed gas nozzle opening 5 and the liquidoutlet opening 7 are accommodated in the shown embodiment in a nozzlebody 10, which extends into the reservoir 9 and the liquid 8 storedtherein. The embodiment shown in FIG. 1 is also particularlyadvantageous because not just one but two symmetrically arranged outletopenings 7 for the liquid 8 are provided adjacent to the nozzle opening5. Another advantageous embodiment comprises an annular gap or annulargroove surrounding the nozzle opening, which opens adjacent to thenozzle opening 5.

In accordance with the invention, a closing means 11 is provided insidethe housing 3 in the embodiment shown in FIG. 1. The closing means 11closes the nozzle opening 5, for which purpose the closing means 11 isdisposed opposite the nozzle opening 5 in the nebulisation area 3. Theclosing means 11 can assume a position exposing the nozzle opening and aposition closing the nozzle opening.

In FIG. 1, the closing means 11 is shown in the position closing thenozzle opening. In this position, the closing means 11 prevents thecompressed gas from exiting out of the nozzle opening 5 and thus theliquid 8 does not exit from the outlet openings 7 and is not nebulisedeither. Since the nozzle opening 5 is blocked, the pressure in thesupply line 6 increases because the compressed gas source, for examplethe aforementioned compressor, continues to supply the compressed gas,however now against the resistance of the blocked nozzle opening 5.

In FIG. 2, the closing means 11 is shown in the position exposing thenozzle opening; FIG. 2 otherwise corresponds to FIG. 1 and thusreference can inasmuch be made at this point to the description ofFIG. 1. In the position exposing the nozzle opening, the closing means11 is at a distance from the nozzle opening 5 for compressed gas suchthat compressed gas supplied via the supply line exits out of the nozzleopening 5 and liquid exiting out of the outlet opening is nebulised. Thepressure in the supply line 6 thereby decreases to the operatingpressure that is provided by the compressed gas source, for example theaforementioned compressor.

In a preferred design of the device 1 according to the invention, theclosing means 11, when in the position exposing the nozzle opening, alsoacts as a baffle, upon which the exiting compressed gas and nebulisedliquid impinge. The advantageous effects of such baffles, which are alsoreferred to as gas flow controls, in the outlet area of openings 5 and 7of the nebuliser nozzle 10 are known to the person skilled in the art.By designing the known gas flow control so as to be moveable between aposition exposing the nozzle opening and a position closing the nozzleopening in order to act as a closing means 11, a particularlyadvantageous design of the inhalation therapy device 1 according to theinvention is achieved.

In order to bring the closing means 11 into the position closing thenozzle opening during the patient's exhalation phases in accordance withthe invention, an actuation device 12 is provided in the embodimentshown in FIGS. 1 and 2 to cause movement of the closing means 11 out ofthe position exposing the nozzle opening and into the position closingthe nozzle opening. The actuation device 12 thereby responds to therespiratory cycle of the patient in order to actuate the closing means11 during the exhalation phase of a respiratory cycle of the patientsuch that the nozzle opening 5 is blocked.

It is achieved according to the invention owing to the cooperation ofthe closing means 11 and the actuation device 12 that aerosol generationis interrupted during the exhalation phases of the respiratory cycle ofa patient and that aerosol is provided to the patient during theinhalation phases. Different positive effects are thereby achieved as aresult of interrupting aerosol generation according to the invention byclosing the nozzle opening 5 for the compressed gas. Aerosol productionis on the one hand immediately interrupted without the reaction times ofthe compressed gas source, for example the compressor, leading toundesirable delays. The closing means acts so quickly on the nozzleopening 5 that interruption occurs almost instantly. On the other hand,in the advantageous case that the exiting compressed gas draws theliquid to be nebulised, exiting of the liquid 8 to be nebulised alsostops almost simultaneously with the interruption of the exiting of thecompressed gas since the drawing action on the liquid 8 also ceases toapply just as instantly as the flow of compressed gas is interrupted.Finally, blocking of the nozzle opening leads to a pressure increase inthe supply line 6, which results in improved aerosol productionfollowing reopening of the nozzle opening. This is because an increasedpressure and an amount of compressed air buffered in the supply line areavailable for a short time following reopening.

The actuation device can be realised in different manners.

In the embodiment shown in FIG. 1, the actuation device 12 comprises aconnecting member 13 that is on the one hand connected with the closingmeans 11 and on the other hand with a piston member 14. The pistonmember 14 is disposed in a cylindrical member 15 so as to enclose acompression space 16 that is ventilated by a ventilation passage 17.Furthermore, a spring member 18 is disposed in the compression space 16,which brings the piston member 14 into a defined rest position.

If the piston member 14 is in the rest position that it assumes owing tothe action of the spring member 18, the closing means 11 is then in theposition exposing the nozzle opening since the piston member 14 isconnected to the closing means 11 via the connecting member 13. Thispositioning of the piston member 14, the connecting member 13 and theclosing means 11 is shown in FIG. 2.

If the patient exhales into the housing 2 of the inhalation therapydevice 1 according to the invention, the pressure in the nebulisationarea 3 increases since an inhalation valve member 20, which isconfigured in the shown embodiment as a flat annular disk made of aflexible material, closes an inlet opening 21 for ambient air. Owing tothe increase in pressure, the piston member 14 is shifted against theaction of the spring member 18 in such a manner that the closing means11 is moved via the connecting member 13 into the position closing thenozzle opening. This positioning of the piston member 14, the connectingmember 13 and the closing means 11 is shown in FIG. 1.

The ventilation passage 17 allows the air present in the compressionspace 16 to escape when the piston member 14 is moved out of the restposition. Furthermore, ambient air subsequently flows through theventilation passage 17 into the compression space 16 when the pistonmember returns to the rest position. It is therefore achieved by meansof the ventilation passage 17 that the forces required for movement ofthe piston member and thus the pressure that causes movement of thepiston member 14 can be defined very precisely by means of the springmember 18.

As shown in FIGS. 1 and 2, the connecting member 13 is preferablyarranged in the shown embodiment in a guide member 19, which is attachedto the cylindrical member 15 and is preferably configured integrallytherewith. Owing to the guide member 19, a stable guiding of theconnecting member 13 is achieved on the one hand, so that reliabletransmission of the movement of the piston member 14 of the actuationdevice 12 to the closing means 11 occurs. On the other hand, the guidemember 19 facilitates sealing of the compression space 16 of theactuation device 12. A corresponding sealing of the compression space 16is additionally also to be ensured at the contact point between thecylindrical member 15 and the piston member 14.

In the shown embodiment, the connecting member 13 is extended beyond theposition of the piston member 14. The ventilation channel 17 ispreferably also formed in this section. The connecting member 13therefore protrudes out of the housing 2 and thereby serves as a visualindicator for the position of the closing means 11.

In the embodiment shown in FIGS. 1 and 2, the actuation device 12 isadvantageously disposed in a supply air duct 22 of the inhalationtherapy device 1, via which supply air, which flows in from theenvironment through the inlet openings 21 when the inhalation valve isopen during the inhalation phases of the patient, is guided into an areain the direct vicinity of the nozzle opening 5 and the outlet openings7. The closing means 11 is also located here, which is moved to and frobetween the two positions by the connecting means 13 depending on therespiratory cycle of the patient.

In the embodiment shown in FIGS. 1 and 2, a respiratory air outletopening 23 is advantageously provided, via which the air exhaled intothe device can escape from the housing 2 during exhalation phases. Thepressure that builds up in the interior of the housing during exhalationand that is required for movement of the closing means 11 can be definedby the design of the shape, the progression and the diameter of therespiratory air outlet opening 23. It must be noted in this regard thata positive influence on the inhalation therapy is also possible in thismanner since often an increased expiration resistance is desired. It isfurthermore possible in this manner, in coordination with the appliedspring force of the spring member 18, to also define the pressure atwhich the closing means 11 is moved back into the position exposing thenozzle opening. The time of exposure can thus be set just before thestart of the inhalation phase, i.e. still in the exhalation phase, suchthat sufficient aerosol is provided to the patient already at the startof the inhalation phase.

In the embodiment shown in FIGS. 1 and 2, the closing means 11 is formedintegrally with the connecting member 13 of the actuation device 12. Analternative design is provided in FIG. 3, which shows a section of therepresentation in FIGS. 1 and 2 in the region of the openings of thenozzle body 10. According thereto, the closing means 11 is not producedintegrally with the connecting means. This design is advantageousinsofar as the material of the closing means 11 can be selectedindependently of the material of the connecting member 13. In order toensure a good sealing of the nozzle opening 5, the closing means 11, orthe part thereof that comes into contact with the nozzle body 10 at thenozzle opening 5, is preferably made from a comparatively soft andflexible material. Soft and flexible materials are often not suitablefor producing the connecting member 13 that has to be rigid for theaction on the closing means 13 and the transmission of forces associatedtherewith.

FIG. 4 shows a design according to the invention, in which a sealingportion 24 made of a soft, flexible material is provided on the nozzlebody 10. Just like in the design according to FIG. 3 as described above,a very good seal is achieved in this manner.

A soft and flexible material can obviously be provided on both theclosing means 11 and the nozzle opening 5, which corresponds to acombination of the two designs of FIGS. 3 and 4.

FIGS. 5 and 6 show a further embodiment of an inhalation therapy device1 according to the invention. A closing means 11 that can assume aposition blocking the nozzle opening, as shown in FIG. 5, and a positionexposing the nozzle opening, as shown in FIG. 6, is also provided inthis embodiment, the structure of which corresponds in many aspects tothe embodiment described above such that reference can be made to theprevious description. The closing means 11 is moved from one positioninto the other and back again by an actuation device 12.

The actuation device 12 comprises a connecting member 13 and a pistonmember 14, which is connected to the connecting member 13 and isdisposed in a cylindrical member 15. Differing from the embodimentdescribed above, the piston member is equipped with an inlet opening 21in the embodiment according to FIGS. 5 and 6, which allows ambient airto flow into the interior of the inhalation therapy device 1 during theinhalation phases. The inlet opening 21 is closed during the exhalationphases by a valve member 20; only a respiratory air outlet opening 23 inthe piston member 14, which is preferably provided, allows respiratoryair to escape under precisely defined conditions. It is thus ensured,for example, that there is sufficient pressure inside the device duringthe exhalation phase to shift the piston member 14 in the cylindricalmember 15 into the position shown in FIG. 5. The piston member 14assumes this position against the reset force of a spring member 18which otherwise moves the piston member 14 into the position shown inFIG. 6.

Since, in the embodiment according to FIGS. 5 and 6, the connectingmember 13 is connected to the closing means 11 via a reversing element25, the closing means 11 assumes the position closing the nozzle openingaccording to FIG. 5 when the patient exhales into the inhalation therapydevice. On the other hand, the closing means 11 is moved into theposition exposing the nozzle opening, as shown in FIG. 6, when thepatient inhales since the piston member 14 is moved into the restposition owing to the action of the spring member 18. The result of thisis that the connecting member 13 moves the closing means 11 via thereversing element 25 into the position exposing the nozzle opening.

In the embodiment shown in FIGS. 5 and 6, part of the housing 2 canreplace the cylindrical member 15 since the piston member 14 canobviously also easily perform the shifting movement along the inner wallof the housing 2.

FIGS. 7 and 8 show a further embodiment of an inhalation therapy device1 according to the invention. A closing means 11 that can assume aposition closing the nozzle opening, as shown in FIG. 7, and a positionexposing the nozzle opening, as shown in FIG. 8, is also provided inthis embodiment, the structure of which corresponds in many aspects tothe embodiments described above such that reference can be made to theprevious description. The closing means 11 is moved from one positioninto the other and back again by an actuation device 12.

The actuation device 12 comprises a connecting member 13 and a pistonmember 14 that is connected with the connecting member 13 and isdisposed in a housing 2 of the device 1 in such a manner that it canmove along the inner wall of the housing 2 as if it were in a cylinder.Deviating from the embodiments described above, the piston member isequipped with a sliding portion 26 in the embodiment of FIGS. 7 and 8,which surrounds a supply air duct 22 of the device 1 and gives thepiston member 14 stability during its shifting movement. A spring member18 is mounted on the supply air duct, which moves the piston member 14into its rest position when the patient does not provide by exhalationinto the device 1 a sufficient pressure in the interior of the device toshift the piston member 14 into the position shown in FIG. 7. When thepiston member 14 is in this position, the closing means 11 that isconnected with the connecting member is in the position blocking thenozzle opening.

In the inhalation phases, the piston member 14 moves into the positionshown in FIG. 8 owing to the action of the spring member 18, such thatthe closing means 11 is in the position exposing the nozzle opening.Furthermore, during the inhalation phases, the aerosol together with thesupply air that has flown in via the supply air duct flows through athrough-hole 27 that is closed during the exhalation phases by means ofa valve member 28. In the exhalation phases, the respiratory air flowsthrough the respiratory air outlet opening 23 described in detail above;reference is herewith made to this description.

Shown in FIGS. 9A and 9B is a partial area of a further embodiment of aninhalation therapy device according to the invention, with essentiallyonly those elements being shown in this section that are required toexplain the differences to the embodiments described above. Thedifferences will be dealt with in the following; reference is otherwisemade to the above description.

In the embodiment according to FIGS. 9A and 9B, the closing means 11 isarranged to the side of a nozzle body 10 that is formed, at leastpartly, from a soft, flexible material. The nozzle body 10 comprises thenozzle opening 5 for the compressed air and the outlet opening 7 for theliquid to be nebulised, the outlet opening 7 being realised in theembodiment shown herein in the form of an annular gap surrounding thenozzle opening. The use of a soft, flexible material allows the nozzlebody 10 to be deformed by the action of the closing means 11 to such anextent that the nozzle opening 5 is closed. Shown in FIG. 9B is theclosing means 11 in the position closing the nozzle opening, into whichthe closing means 11 is brought by means of the actuation device 12 (notshown in FIG. 9B) depending on the breath of the patient. On the otherhand, FIG. 9A shows the closing means 11 in the position exposing thenozzle opening. As is apparent, there is no deformation of the nozzlebody 10 since the closing means is not acting on the nozzle body 10.

FIGS. 10A and 10B show a further embodiment of an inhalation therapydevice according to the invention, with FIGS. 10A and 10B again alsobasically only showing those elements that are required to explain thedifferences to the embodiments described above. These differences willbe dealt with in the following; reference is otherwise made to the abovedescription.

It must be noted with regard to FIGS. 10A and 10B that they show a topview of the nozzle head 10 with the nozzle opening 5 and the outletopenings 7. The symmetrical arrangement of the outlet openings 7adjacent to the nozzle opening 5 as described above is clearly apparent.The closing means 11 is also disposed to the side of the nozzle head 10in the embodiment according to FIGS. 10A and 10B. FIG. 10A shows theclosing means 11 in the position exposing the nozzle opening 5, whereasthe closing means 11 in FIG. 10B is shown in the position closing thenozzle opening. The closing means 11 is moved to and fro between thesetwo positions by the actuation device 12 (which is not shown in FIGS.10A and 10B) depending on the breath of the patient.

1. Inhalation therapy device for the provision of an aerosol for use bya patient as part of an inhalation therapy, said device comprising: ahousing that defines a nebulisation area, at least one nozzle openingfor the entry of a pressurised gas, preferably compressed air, into thenebulisation area, at least one outlet opening for the entry of a liquidto be nebulised, preferably a therapeutically effective liquid, into thenebulisation area, a closing element for closing the nozzle opening,which is arranged in the nebulisation area relative to the nozzleopening such that the closing element can be moved into a positionclosing the nozzle opening and into a position exposing the nozzleopening.
 2. Inhalation therapy device according to claim 1, wherein saidclosing of said nozzle opening by said closing element leads to apressure increase in a supply line and in an improved aerosol productionfollowing reopening the nozzle opening by said closing element. 3.Inhalation therapy device according to claim 1, further comprising anactuation device for actuating the closing element in response to arespiratory cycle of the patient so as to actuate the closing elementduring an exhalation phase of the respiratory cycle of the patient suchthat the closing element assumes the position closing the nozzleopening.
 4. Inhalation therapy device according to claim 1, wherein theclosing element is disposed opposite the nozzle opening.
 5. Inhalationtherapy device according to claim 1, wherein in the position exposingthe nozzle opening, the closing element forms a baffle for thecompressed gas exiting out of the nozzle opening and the liquid exitingout of the outlet opening.
 6. Inhalation therapy device according toclaim 1, wherein the closing element is disposed to the side of thenozzle opening.
 7. Inhalation therapy device according to claim 1,wherein the closing element for closing the nozzle opening acts on anozzle body made of a soft, flexible material, in which the nozzleopening is formed.
 8. Inhalation therapy device according to claim 1,wherein the closing element is made at least partly of a soft andflexible material.
 9. Inhalation therapy device according to claim 1,wherein a sealing portion made of a soft and flexible material isprovided at the nozzle opening.
 10. Inhalation therapy device accordingto claim 3, wherein the actuation device comprises a connecting elementthat connects the actuation device to the closing element. 11.Inhalation therapy device according to claim 3, wherein the actuationdevice comprises a piston member, the pressure prevailing in the housingdetermining the position of the piston member.
 12. Inhalation therapydevice according to claim 11, wherein the actuation device comprises aspring member that determines the rest position of the piston member.13. Inhalation therapy device according to claim 12, wherein theactuation device comprises a cylindrical member and wherein the springmember is disposed in the compression space that is enclosed by thepiston member and the cylindrical member.
 14. Inhalation therapy deviceaccording to claim 13, wherein the cylindrical member is formed by thehousing.
 15. Inhalation therapy device according to claim 10, whereinthe connecting element is connected to a piston member.
 16. Inhalationtherapy device according to claim 15, wherein the connecting element isextended beyond the piston member such that the connecting elementprotrudes out of the housing.
 17. Inhalation therapy device according toclaim 13, wherein a ventilation passage is provided for the inlet of airto and the outlet of air from the space enclosed by the piston memberand the cylindrical member during movement of the piston member in thecylindrical member.
 18. Inhalation therapy device according to claim 10,wherein the actuation device comprises a guide member in which theconnecting element is disposed.
 19. Inhalation therapy device accordingto claim 10, wherein the connecting element is configured integrallywith the closing element.
 20. Inhalation therapy device according toclaim 3, wherein the actuation device is disposed in a supply air ductof the inhalation therapy device.
 21. Inhalation therapy deviceaccording to claim 1, wherein the liquid to be nebulised is stored in aliquid reservoir forming part of the housing.
 22. Inhalation therapydevice according to claim 21, wherein a nozzle body extends into thereservoir and the liquid stored therein.
 23. Inhalation therapy deviceaccording to claim 1, wherein, in the position closing the nozzleopening, the closing element prevents pressurised gas from exiting outof the nozzle opening and prevents entry of the liquid to be nebulised.24. Inhalation therapy device according to claim 1, wherein, in theposition exposing the nozzle opening, the closing element is at adistance from the nozzle opening such that liquid exiting out of the atleast one outlet opening adjacent to the nozzle opening is nebulised.25. Inhalation therapy device according to claim 10, wherein a materialof the connecting element is selected independently from a material ofthe closing element.
 26. Inhalation therapy device according to claim 3,wherein the actuation device comprises a piston member equipped with aninlet opening, wherein the inlet opening is closed during the exhalationphase to ensure sufficient pressure inside the device during theexhalation phase.